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Keywords:

  • myocardial;
  • triglycerides;
  • spectroscopy

Abstract

  1. Top of page
  2. Abstract
  3. MATERIALS AND METHODS
  4. RESULTS
  5. DISCUSSION
  6. REFERENCES

Accumulation of triglycerides (TG) in heart tissue has been associated with changes in left ventricular function. Proton magnetic resonance spectroscopy is currently the only noninvasive in vivo method to measure myocardial triglycerides content. The primary aim of this study was to determine if these in vivo measurements are specific to myocardial triglycerides in human subjects. Thus, in vivo proton magnetic resonance spectroscopy measurements were conducted on orthotopic heart transplant patients (n = 8) immediately before they underwent routine biopsies and ex vivo measurements were made on the endomyocardial biopsy samples. The correlation coefficient between the two measurements was 0.97, with P < 0.005, demonstrating for the first time the specificity of the in vivo measurement in human heart. From accompanying reliability experiments, the standardized typical error for the in vivo proton magnetic resonance spectroscopy method was estimated to be 7.0%, with a 95% confidence interval from 5.5 to 9.4%. These results suggest that proton magnetic resonance spectroscopy provides a specific and reliable measurement of myocardial triglycerides content and is suitable for routine studies. Magn Reson Med, 2011. © 2011 Wiley-Liss, Inc.

Abnormalities in myocardial fatty acid metabolism are central to the pathogenesis of obesity and diabetic cardiomyopathies (1–4). Typically, fatty acid uptake exceeds oxidation, leading to the accumulation of intramyocellular triglyceride (TG) within the heart. The increased myocardial deposition of TG can have numerous detrimental effects on myocellular health including reduced insulin sensitivity, increased oxidative stress, stimulation of cell death pathways, and systolic and diastolic dysfunction (4–6). In humans, in vitro measurements of myocardial TG content have been shown to be directly correlative with the presence of obesity- and diabetes-related heart failure (7). Thus, quantitative and reliable techniques to monitor in vivo TG accumulation in heart are important for disease diagnosis and management.

Localized 1H magnetic resonance spectroscopy (MRS) is currently the only noninvasive in vivo method to measure TG content in tissue (8–11). MRS measurements of myocardial TG levels have been shown to be an independent predictor of diastolic function in patients with diabetes and are responsive to changes in fatty acid delivery to the heart (12, 13). The validity of the method in the human heart is based on nonlocalized MRS measurements from excised rodent heart that correlated with biochemical measurements (9, 14). However, the specificity of the method in human heart is unproven. Accordingly, the primary goal of this study was to determine if a similar correlation exists between in vivo MRS-derived and ex vivo measurements in the human heart. To achieve this aim, we first determined the reliability of our MRS protocol with test–retest measurements. Then, we compared in vivo MRS measurements with ex vivo measurements from biopsy tissue from the same heart and proximate location. Chemical extracts for biochemical or mass spectrometry TG assays were not possible due to the small biopsy size (∼2 mg). Therefore, we used magic angle spinning (MAS) and high-resolution MRS, which have been validated against biochemical measurements, to quantify TG in ex vivo samples (9, 14, 15).

MATERIALS AND METHODS

  1. Top of page
  2. Abstract
  3. MATERIALS AND METHODS
  4. RESULTS
  5. DISCUSSION
  6. REFERENCES

These studies were HIPAA-compliant and approved by the Human Research Protection Office at Washington University School of Medicine, and the study participants signed an approved informed consent document.

Study Subjects

Ten control subjects with a broad range of body mass indexes (28 ± 6 kg m−2) and physiological conditions (normal, obese, diabetic, and HIV) underwent multiple repeat MRS measurements in the same magnet session to determine the reproducibility of the method. The study was repeated 2 to 10 days later in seven of these subjects. Nine heart transplant patients who were scheduled for routine endomyocardial biopsy for allograft rejection surveillance were also scanned to correlate in vivo and ex vivo measurements. These subjects had no clinical evidence of active rejection at the time of the study and were scanned immediately before the biopsy to eliminate any effects of inflammation and bleeding. To further test reproducibility, multiple measurements were performed on six of the transplant subjects during the same magnet session. Values reported in the in/ex vivo correlation are an average of these measurements. Standard contraindications to MRI and an age of less than 18 years were the only other exclusion criteria.

In vivo MRS

Human studies were performed on a Siemens 1.5T MAGNETOM Sonata (Siemens Medical Systems, Erlangen Germany), with the body coil used as the transmitter and an eight-element body array coil used for reception. Short- and long-axis true-FISP images for voxel positioning were obtained during free breathing with both ECG and two-dimensional prospective acquisition correction respiratory gating. The ECG gating was chosen to correlate with the end systolic period and the navigator had a 2-mm acceptance window near end expiration. The spectroscopy data was collected with a similarly gated point-resolved spectroscopy sequence with a 6 × 20 ×20 mm3 volume of interest placed in the intraventricular septum (16, 17). To minimize outer volume contamination, a 90° SLR excite pulse with a bandwidth time product of 13.1 and MAO refocusing pulses with bandwidth time products of 6.0 were used (18, 19). Additionally, the first and second MAOs were saddled by crushers with 80 and 150× residual signal suppression, respectively, regardless of voxel size or orientation (20). The sequence also alternated the gradient polarity every scan and used a COG5(2,3,2:0) phase cycle. The specific MRS acquisition parameters that were used were: the relaxation delay was defined by the length of respiratory cycle, ∼4 sec; echo delay = 24 msec, averages = 120 in blocks of 60 with localization verification in between, spectral width = 2 kHz, 512 data points, and a transmitter frequency of 2.9 ppm. Siemens automatic shimming was preformed before acquisition under breath hold. In general, subjects were not removed from the magnet, just relocalized with minor voxel adjustments, for each group of 120 averages.

The in vivo data were processed and analyzed using the AMARES algorithm within the jMRUI 3.0 software package (21, 22). Briefly, the water resonance was first used to estimate the line shape. Then, the lipid resonances were constrained with a similar shape and other prior knowledge (16). The in vivo TG content is presented as the ratio of the sum of the areas from the methyl and methylene resonances to the area from the H2O resonance times 100—an approximate percentage.

Endomyocardial Biopsy

Immediately after the MRS study, the heart transplant subjects underwent endomyocardial biopsy. An additional right ventricular septal endocardial biopsy (2.3 ± 1.3 mg) was obtained using standard clinical procedures. The biopsy sample was immediately frozen in liquid nitrogen and stored at −80°C for ex vivo TG analysis.

Ex Vivo Analysis

MAS MRS analysis was done at 400.5 MHz using a Tecmag (Houston, TX) Apollo console and a Doty Scientific (Columbia, SC) 4-mm double resonance probe. The high-resolution MRS (HR) analysis of the biopsy samples was done at 599.5 MHz using a Varian (Palo Alto, CA) Unity Inova console and a 5-mm, three-axis gradients (not used), triple resonance probe. Both MAS and HR spectra were acquired using a spin-echo sequence with TR = 4 sec and echo delay = 24 msec, with pulse widths verified using the H2O signal of the samples. The minor variations in the 180° widths (0.1 μsec) suggest that the receptivities of the spectrometers were relatively constant. Thermogravimetric analysis (TGA) was done with a Mettler Toledo (Columbia, MA) 50T/A851e TGA.

Biopsies were first blotted dry with a chem-wipe, weighed (TGA), put in a MAS rotor, and spun at ∼4 kHz. Room temperature shims were not available. Sixty-four acquisitions were acquired at room temperature. Samples were refrozen immediately after acquisition. All MAS acquisitions took place sequentially on the same day. Each sample was next put into an HR tube with ∼300 mg of D2O (occupying ∼70% of the coil length), spun at 20 Hz, and shimmed. One hundred twenty-eight acquisitions were acquired at 37°C. For HR, two groups of samples were run for which general spectrometer performance was accounted for with a common H2O/D2O standard.

The small biopsy size and resulting large surface to volume ratio made scaling the area of the TG resonance by either the H2O resonance area or wet weight inconsistent. Thus, after the HR acquisition, the dry weight of the biopsy was determined via TGA analysis in a nitrogen atmosphere with the temperature increased to and left at 90°C until a constant weight was achieved, typically 2 to 4 h. The ex vivo lipid concentration is presented as the area of the TG methylene resonance from 1.15 to 1.25 ppm, determined as reported previously, scaled by the dry weight of the sample (14). All of the MAS areas were additionally scaled by a common factor to approach the HR scale.

Statistical Analysis

Correlations were calculated by linear regression, with a P value less than 0.05 considered statistically significant. The intraclass correlation coefficient (no agreement), measurement (typical) and standardized typical error (STE), along with correspsonding 95% confidence intervals were calculated as described by Hopkins from the log-transformed data (23, 24). The Kendall tau rank correlation was calculated via Mathematica™. Assessment of reliability was also determined by the methods outlined by Bland and Altman, with the coefficient of reliability listed as twice the standard deviation of the measurement differences (25). In the above calculations, all permutations of repeated intrasubject measurements were considered. Results are expressed as mean ± standard deviation or value (confidence interval).

RESULTS

  1. Top of page
  2. Abstract
  3. MATERIALS AND METHODS
  4. RESULTS
  5. DISCUSSION
  6. REFERENCES

Reproducibility

All in vivo spectra had a signal to noise ratio >5, determined using peak height, for the TG resonance and the half-height full-width line width <0.3 ppm for the water peak. All intrasubject retest (1.3 ± 0.6% TG) permutations (1 versus 2, 1 versus 3, 2 versus 3, etc.) are shown in Figure 1, along with the corresponding Bland-Altman plot of the differences (−0.029 ± 0.09%). Two measurements produced differences outside of 0.15 to −0.21 (±2.standard deviation) and were removed, leaving 60 retest measurements from which all further results are based and whose 53 differences are characterized by −0.029 ± 0.07%. The removed measurements were both the final measurements from long sessions, one the third of the first subject and the other the fifth. The Kendall tau rank correlation between the intrasubject mean and standard deviation is 0.16. The log-transformed data have an intraclass correlation coefficient of 0.99 (0.98–1.0) and a typical error and STE coefficients of variation of 5.1 (4.0–7.0)%, and 7.0 (5.5–9.4)%, respectively. The STE coefficient of variation from the nontransformed data was 7.4 (5.9–10.0)%.

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Figure 1. Reliability of the ECG and respiratory-gated proton magnetic resonance spectroscopy measurement of intramyocellular TG with all permutations of intrasubject measurements plotted. The line is a guide with unity slope. The inset shows the corresponding Bland-Altman plot, with the difference between two intrasubject measurements plotted against the subject mean. The dashed lines are ±2·standard deviation, and the solid line is the mean of the differences.

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In vivo versus ex vivo

Figure 2 shows example in vivo and ex vivo (MAS and HR) spectra taken from one subject and Fig. 3 shows all of the in vivo and corresponding HR spectra. The in vivo myocardial TG content in transplant subjects was on average 0.4 ± 0.2%. The correlations between the in vivo and ex vivo MAS (r2 = 0.83) and HR (r2 = 0.97) measurements are shown in Fig. 4. Because the shims were inoperable, MAS was not used for the second group of samples and further discussion will refer to the HR results. The ex vivo analysis of the smallest biopsy sample (0.15 mg, dry) was 1/2 of that expected, deemed an outlier, and not included in the analysis.

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Figure 2. The figure shows the spectra obtained from the in vivo and ex vivo experiments of one transplant subject. The pertinent resonances in the figure are water (4.6 ppm), methylene (1.2 ppm), and methyl (0.9 ppm). The top spectrum is from in vivo proton magnetic resonance spectroscopy, with the light, coincident line the AMARES fit to the spectrum. The middle and bottom spectra are from ex vivo 400 MHz MAS and 600 MHz HR, respectively. The increased line-width in the MAS compared to the HR spectrum results from inoperable shims. The upper left image shows the location and size of the voxel in the intraventricular septum.

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Figure 3. The figure shows TG-region expansions from all of the in vivo proton magnetic resonance spectroscopy (left) and ex vivo HR (right) transplant spectra. The in vivo spectra are scaled by their H2O-resonance area, and the ex vivo spectra are scaled by their dry weight and other spectrometer related factors as described in the text. For visual clarity, the H2O resonance was removed from the in vivo spectra using the jMRUI SVD filter. Gaussian line-broadening (5 and 20 Hz) was applied to the in vivo and ex vivo spectra, respectively.

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Figure 4. In vivo proton magnetic resonance spectroscopy responses versus the corresponding ex vivo MAS (○, r2 = 0.83, P = 0.005) and HR (•, r2 = 0.97, P = 10−5) measurements from endomyocardial biopsies. The lines result from the regression analysis. The MAS results are not ideal primarily because the shims were inoperable, resulting in spectra with lower SN and resolution than the HR spectra (Fig. 2).

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DISCUSSION

  1. Top of page
  2. Abstract
  3. MATERIALS AND METHODS
  4. RESULTS
  5. DISCUSSION
  6. REFERENCES

Proton magnetic resonance spectroscopy (1H MRS) is an invaluable tool for studying in vivo TG changes; however, this use has never been correlated against in vitro human myocardial TG measurements. This study was undertaken to determine if 1H MRS does specifically measure the TG concentration in human myocardium or if the measurement is contaminated by nearby TG and H2O. For this correlation, we first characterized the reliability of the technique. With an STE = 8% and data from eight transplant subjects, regression correlations greater than ∼0.85 are statistically significant (α = 0.01, β = 0.05) (23, 26). Thus, the correlation between measurements from in vivo 1H MRS and ex vivo biopsies from the same heart shows that 1H MRS gated by motion and ECG does specifically measure the relative TG concentration in beating human hearts.

There are several factors that could have affected the in/ex vivo correlation, of which tissue heterogeneity may be the most prominent. The in vivo MRS measurements were obtained from a large (2.4 cm3) region in the intraventricular septum. In contrast, the biopsy samples were small (∼2 mg) and from the septum wall. There is a paucity of data regarding a potential heterogeneous myocellular TG distribution in the human septum. The correlation in our data suggests that MRS sampling of a large voxel in the intraventricular septum is similar to that of the septum wall and not contaminated by epicardial fat or blood.

The slope in the correlation was not expected to be unity for several reasons. First, the tissue relaxation is different due to the different magnetic field strengths. Accurately measuring and accounting for these differences was not possible due to time restrictions. However, considering that the type and rate of molecular motion for the TG molecules in small micelles, on which relaxation depends, is vastly homogeneous throughout the population, the differences should also be homogeneous, and should have little impact on the correlation. Similarly, because of the general homogeneous nature of myocellular tissue water content, the different ratios reported for the in vivo and ex vivo measurements also primarily affect the slope.

We also observed a constant offset between the in vivo and ex vivo measurements (nonzero intercept). Physiologically, it is unlikely that the various-sized biopsies would contain a constant fraction of endocardium with endothelial cells high in TG. A more likely explanation is that a small fraction of TG is lost in the deconvolution of the broader in vivo TG and H2O resonances. This possibility is supported by the intercept trending to zero as only higher TG ratios are used in the regression. It should be emphasized that in our measurements, the signal to noise ratio was consistently >5 for the TG resonance, calculated via peak height, and the half-height full-width line width was ≤0.3 ppm for the water resonance, two criteria we consider necessary to achieve a STE ∼ 7%.

The MRS approach used in this study and the estimated STE are both similar to those of previous studies (9, 27, 28). However, the sequence and protocol do use some modifications that result in consistent spectral quality and, concerning specificity, outer volume contamination. Thus, the correlation and STE may only hold for approaches with similar spectral and localization integrity.

In summary, the in vivo MRS measurement for myocardial TG had excellent, statistically significant correlation with ex vivo TG measurements from biopsy samples taken from the same subjects. This correlation demonstrates that 1H MRS specifically measures in vivo human myocardial TG. Furthermore, considering the measurement error, the technique should be a reliable tool for monitoring the effects interventions in metabolic or cardiac studies.

REFERENCES

  1. Top of page
  2. Abstract
  3. MATERIALS AND METHODS
  4. RESULTS
  5. DISCUSSION
  6. REFERENCES
  • 1
    Diamant M, Lamb HJ, Groeneveld Y, Endert EL, Smit JW, Bax JJ, Romijn JA, de Roos A, Radder JK. Diastolic dysfunction is associated with altered myocardial metabolism in asymptomatic normotensive patients with well-controlled type 2 diabetes mellitus. J Am Coll Cardiol 2003; 42: 328335.
  • 2
    Opie LH. The metabolic vicious cycle in heart failure. Lancet 2004; 364: 17334.
  • 3
    Peterson LR, Herrero P, Schechtman KB, Racette SB, Waggoner AD, Kisrieva-Ware Z, Dence C, Klein S, Marsala J, Meyer T, Gropler RJ. Effect of obesity and insulin resistance on myocardial substrate metabolism and efficiency in young women. Circulation 2004; 109: 21912196.
  • 4
    Virkamäki A, Korsheninnikova E, Seppälä-Lindroos A, Vehkavaara S, Goto, T, Halavaara J, Häkkinen A, Yki-Järvinen H. Intramyocellular lipid is associated with resistance to in vivo insulin actions on glucose uptake, antilipolysis, and early insulin signaling pathways in human skeletal muscle. Diabetes 2001; 50: 23372343.
  • 5
    Unger R. Lipotoxic diseases. Annu Rev Med 2002; 53: 319336.
  • 6
    Zhou Y, Grayburn P, Karim A, Shimabukuro M, Higa M, Baetens D, Orci L, Unger R. Lipotoxic heart disease in obese rats: implications for human obesity. PNAS 2000; 97: 17841789.
  • 7
    Sharma S, Adrogue JV, Golfman L, Uray I, Lemm J, Youker K, Noon GP, Frazier OH, Taegtmeyer H. Intramyocardial lipid accumulation in the failing human heart resembles the lipotoxic rat heart. FASEB J 2004; 18: 16921700.
  • 8
    Boesch C, Machann J, Vermathen P, Schick F. Role of proton MR for the study of muscle lipid metabolism. NMR Biomed 2006; 19: 968988.
  • 9
    Szczepaniak LS, Dobbins RL, Metzger GJ, Sartoni-D'Ambrosia G, Arbique D, Vongpatanasin W, Unger R, Victor RG. Myocardial triglycerides and systolic function in humans: in vivo evaluation by localized proton spectroscopy and cardiac imaging. Magn Reson Med 2003; 49: 417423.
  • 10
    Thomas EL, Hamilton G, Natel N, O'Dwyer R, Dore CJ, Goldin RD, Bell JD, Taylor-Robinson SD. Hepatic triglyceride content and its relation to body adiposity: a magnetic resonance imaging and proton magnetic resonance spectroscopy study. Gut 2005; 54: 122127.
  • 11
    Torriani M, Thomas BJ, Halpern EF, Jensen ME, Rosenthal DI, Palmer WE. Intramyocellular lipid quantification: repeatability with 1H MR spectroscopy. Radiology 2005; 236: 609614.
  • 12
    McGavock JM, Lingvay I, Zib I, Tillery T, Salas N, Unger R, Levine BD, Raskin. P, Victor RG, Szczepaniak LS. Cardiac steatosis in diabetes mellitus A 1H-magnetic resonance spectroscopy study. Circulation 2007; 116: 11701175.
  • 13
    van der Meer RW, Rijzewijk LJ, de Jong HW, Lamb HJ, Lubberink M, Romijn JA, Bax JJ, de Roos A, Kamp O, Paulus WJ, Heine RJ, Lammertsma AA, Smit JW, Diamant M. Pioglitazone improves cardiac function and alters myocardial substrate metabolism without affecting cardiac triglyceride accumulation and high-energy phosphate metabolism in patients with well-controlled type 2 diabetes mellitus. Circulation 2009; 119: 20202022.
  • 14
    O'Connor RD, Gropler RJ, Peterson L, Schaffer J, Ackerman JJH. Limits of a localized magnetic resonance spectroscopy assay for ex vivo myocardial triacylglycerol. J Pharm Biomed Anal 2007; 45: 382389.
  • 15
    Schenetti L, Mucci A, Parenti F, Cagnoli R, Righi V, Tosh MR, Tugnoli V. HR-MAS NMR spectroscopy in the characterization of human tissues: application to healthy gastric mucosa. Concepts Magn Reson Part A 2006; 28: 430443.
  • 16
    O'Connor RD, Bashir A, Cade WT, Yarasheski KE, Gropler RJ. 1H-Magnetic resonance spectroscopy for quantifying myocardial lipid content in humans with the cardiometabolic syndrome. J Clin Hypertens 2009; 11: 528532.
  • 17
    Xu J. MRS with free-breathing 2D-PACE (WIP). New York: Siemens Medical Solutions USA Inc.; 2006.
  • 18
    Mao J, Mareci TH, Andrew ER. Experimental study of optimal selective 180° radiofrequency pulses. J Magn Reson 1988; 79: 110.
  • 19
    Cunningham CH, Wood ML. Method for improved multiband excitation profiles using the Shinnar–Le Roux transform. Magn Reson Med 1999; 42: 577584.
  • 20
    Ernst T, Chang L. Elimination of artifacts in short echo time 1H MR spectroscopy of the frontal lobe. Magn Reson Med 1996; 36: 462468.
  • 21
    Naressi A, Couturier C, Devos JM, Janssen M, Mangeat C, de Beer R, Graveron-Demilly D. Java-based graphical user interface for the MRUI quantitation package. MAGMA 2001; 12: 141152.
  • 22
    Vanhamme L, van den Boogaart A, Van Huffel S. Improved method for accurate and efficient quantification of MRS data with use of prior-knowledge. J Magn Reson 1997; 129: 3543.
  • 23
    Hopkins WG. Measures of reliability in sports medicine and science. Sports Med 2000; 30: 115.
  • 24
    Hopkins WG. Reliability spreadsheet, Available at: http://www.sportsci.org. September 2010: a new view of statistics; 2009. Accessed March 2010.
  • 25
    Bland JM, Altman DG. Statistical methods for assessing agreement between two methods of clinical measurement. Biochimica Clinica 1986: 399317.
  • 26
    Lenth RV. Java applets for power and sample size. 3.0: Available at: http://www.stat.uiowa.edu/∼rlenth/Power; 2006. Accessed March 2010.
  • 27
    Reingold JS, McGavock JM, Kaka S, Tillery T, Victor RG, Szczepaniak LS. Determination of triglyceride in the human myocardium by magnetic resonance spectroscopy: reproducibility and sensitivity of the method. Am J Physiol Endocrinol Metab 2005; 289: E935E939.
  • 28
    van der Meer RW, Doornbos J, Kozerke S, Schär M, Bax JJ, Hammer S, Smit JWA, Romijn JA, Diamant M, Rijzewijk LJ, de Roos A, Lamb HJ. Metabolic imaging of myocardial triglyceride content: reproducibility of 1H MR spectroscopy with respiratory navigator gating in volunteers. Radiology 2007; 245: 251257.